PET Myocardial Imaging:

15O is cyclotron produced by the irradiation of nitrogen [¹⁴N (d,n) ¹⁵O or ¹⁵N(p,n)¹⁵O] and it has a physical half-life of only 2.2 minutes (123 seconds). O-15 produced in the cyclotron is converted to [¹⁵O]CO₂ by passing it over activated charcoal at 400 to 600 degrees Celsius. [O-15] water is then prepared by bubbling the [¹⁵O]CO₂ into water. Theoretically, ¹⁵O water is ideal for quantitative regional myocardial flow measurements (in ml/min/gm) for two reasons: it is a freely diffusible perfusion tracer with 100% extraction by the myocardium [29], and it is not affected by metabolic factors. The positron range is about 1.1 mm [44].

The extraction of oxygen-15-water (H2¹⁵O) remains linear even at very high flow rates (it is the only perfusion tracer with linear extraction- meaning its accumulation in tissue is almost exclusively a function of blood flow [44]) and, therefore, myocardial distribution of the agent reflects regional perfusion. Unfortunately, image quality is not as good as that obtained with other flow agents because tracer circulating in the blood pool remains within the ventricular chamber and must be subtracted in order to visualize the myocardium. This can be done by use of a separate administration of O-15 carbon monoxide to label erythrocytes or by the use of an early image (20-40 seconds after the administration of O-15 water) which would represent a vascular image before significant activity reaches the coronary arteries [29].

For myocardial perfusion quantification, dynamic scans are obtained for up to 5 minutes after bolus administration of 15-25 mCi [29]. For a typical rest-stress H2¹⁵O exam (2 x 740 MBq) the patient effective radiation dose is about 1.4 mSv [43].

Rubidium-82:

Rubidium-82 (⁸²Rb) is a generator produced positron emitter. Rubidium-82 has a physical half-life of only 75 seconds. The agent is produced from a Strontium-82 generator (T1/2=25.5 days) which decays by electron capture to ⁸²Rb. The generator can therefore be used for about 1 month [44]. The generator can be eluted with a greater than 90% yield every 10 minutes [52]. Rubidium-82 is a potassium analog and tissue uptake requires an active Na/K-ATPase pump for intracellular transport [44]. The short half-life allows for repeat imaging and blood flow measurements in short time intervals, but requires the use of large doses of the tracer. However, the short half-life of the agent has some negative effects as well. First- it is crucial to wait for ⁸²Rb to clear from the blood pool prior to imaging because ⁸²Rb counts in the cavity could scatter into subendocardial defects and obscure them [43]. The time required for clearing of ⁸²Rb from the cardiac blood pool is inversely related to the cardiac output and directly related to the circulation time [43]. Therefore, following injection imaging must be delayed for at least 2 minutes to permit clearance of blood pool activity and considerable decay of the tracer occurs during this time. Also, due to changing myocardial activity from decay, imaging times must be short to prevent back-projection reconstruction artifacts. Another drawback of the agent is that myocardial single-capillary transit extraction of the agent is low- about 50-60% at rest [52] and this further decreases at high flow rates to only 25-30%. However, another article suggests high extraction of ⁸²Rb by the myocardium and that uptake is more linearly related to increases in coronary blood flow than Tc-99m SPECT agents [46]. Myocardial ischemia and reperfusion reduce the uptake of Rb-82 due to a reduction in cellular transport [29]. This reduction in extraction occurs even after only short periods of transient ischemia [29].  ⁸²Rb has the worst resolution of all the positron emitting agents- this is because of it's high positron energy (1.52 MeV) which results in a mean range of about 5.5 mm (2.8-12.4 mm) prior to undergoing an annihilation [44,46].

Radiation dose: The critical organ is the kidney. For a typical rest-stress exam the effective patient dose is about 302-500 mrem (5.0 mSv) [43,46] to 1.6 rem (16 mSv) [45]. The dose is lower or similar to that associated with rest-stress Tc-99m perfusion imaging (approximately 667 mrad) [46].

Exam protocol: Rest imaging should be performed prior to stress imaging to reduce the impact of residual stress effects such as myocardial stunning which can affect Rb-82 extraction [27,29]. Pharmacologic stress using dipyridamole is presently used for ⁸²Rb imaging [42,46]. The longer duration of hyperemia with dipyridamole enables acquisition of three separate image sets- transmission, emission, and ECG-gated [46]. Following the exam, aminophylline 100 mg can be administered to reverse the effects of dipyridamole [46].

On SPECT pharmacologic imaging, ST segment depression during vasodilator infusion has been shown to be associated with an increased risk for subsequent cardiac events even when perfusion imaging was normal [42]. However, a normal ⁸²Rb stress exam confers an excellent prognosis even when ST segment depression is noted [42].

The typical dose for the ⁸²Rb perfusion exam is 40 to 60 mCi (1.48-2.22 GBq) infused over 20 to 30 seconds [27,46,52]. In patients with normal LV function, imaging is usually begun 60-70 seconds (Di Carli recommends 90 sec in healthy individuals) after the infusion is complete to permit clearance of blood pool activity. Imaging is delayed to 90-120 seconds following completion of the infusion in patients with poor LV function (LVEF less than 30%) or RV systolic function [27,52]. About 80% of the useful counts are acquired in the first 3 minutes, and 95% in the first 5 minutes [27].

For a standard 2D acquisition ⁸²Rb cardiac images tend to be count poor due to the agents short half-life [26]. 3D imaging has a higher sensitivity, however, it suffers from greater scatter, random events, and saturation which can paralyze a system [26]. Further work needs to be performed to determine optimal 3D myocardial perfusion imaging [26].

Results: Compared to SPECT imaging, PET imaging with Rb-82 has been shown to be more accurate (87% versus 71% for greater than 50% vessel stenosis), to have fewer artifacts (due to lower bowel and liver activity which affected only 5% of PET studies, but 41% of SPECT exams), and to produce overall higher quality examinations which results in a higher diagnostic confidence (i.e.: a greater number of definitively normal or abnormal exams) [46]. PET imaging was also superior for localizing disease to individual coronary arteries [46]. Identification of multivessel CAD is also superior with PET imaging [46]. As with SPECT imaging, the extent and severity of stress perfusion defects correlate with an increased risk for mortality [52]. Preliminary data indicate that a normal PET exam is associated with a very good prognosis and a low cardiac event rate (0.4% rate of MI or cardiac death) [52]. In one study, the use of PET perfusion imaging in patients with an intermediate probability for coronary artery disease was found to reduce the use of invasive coronary angiography by over 50% (a 30% cost savings) [55]. This was felt to be related to the improved specificity of PET compared to SPECT imaging (false positive exams decreased from 15.6% with SPECT to 5.2% with PET) [55].

However, a normal stress perfusion PET study is an overall poor discriminator of patients without non-flow limiting (subclinical) coronary atherosclerosis [60]. Up to 50% of patients with normal PET perfusion imaging are found to have some degree of CAD by CTA [60]. Therefore, CTA imaging plays a complimentary role to PET perfusion imaging by permitting identification of pre-clinical CAD that can be treated with aggressive medical treatment and life style modification  [60].

Quantitative evaluation: Quantification of blood flow can be performed with Rb-82, but is challenging [52]. Because true determination of absolute perfusion is complex and time consuming, balanced 3-vessel ischemia may still not be readily apparent even in perfusion PET imaging. Unlike SPECT imaging which is performed in a delayed manner, ⁸²Rb PET enables measurement of LV function during peak pharmacologic hyperemia [50]. Even with pharmacologic stress, LVEF increases during vasodilator stress in normal patients [52]. A reduced subendocardial flow reserve or a coronary steal in patients with multivessel disease can lead to myocardial dysfunction with pharmacologic stress and changes in the LVEF [50]. A decrease in LVEF of more than 5% during pharmacologic stress can be seen in patients with severe multivessel CAD [50]. Conversely, an increase in LVEF of more than 5% has a very high negative predictive value for excluding the presence of severe left main or 3-vessel CAD (i.e.: the negative predictive value of a greater than 5% increase in LVEF between rest and stress to exclude the presence of 3-vessel or left-main disease is 97%) [50]. LVEF has been shown to provide additional prognostic information over stress perfusion PET imaging alone [52].

Copper 62 PTSM: Copper-62-Pyruvaldehyde-bis-(⁴N-thiosemicarbazone)

Cu-PTSM is a generator-produced tracer which can also be used for myocardial perfusion imaging. ⁶²Cu has a physical half-life of 9.7 minutes. The short half-life of the parent isotope ⁶²Zn (9.3 hours) limits the practical life of the generator to 1 to 2 days. However, once loaded, the generator can be eluted every 30 minutes. The positron range is 2.7 mm [44].

⁶²Cu -PTSM is a neutral, lipophilic tracer that is taken up in tissues and then trapped intracellularly by reduction to a non-lipophilic compound. There is non-linear extraction of the tracer (ie: extraction decreases at high flow rates) and high liver activity which scatters into the inferior wall. The agent also binds to human albumin which precludes accurate recording of the arterial input function which is critical for quantification. [5] The recommended dose is 0.12-0.2 mCi/kg as an intravenous bolus followed by dynamic imaging for 10-15 minutes [44].

PET Metabolic Imaging

There are numerous clinical applications for PET metabolic myocardial imaging. One of the most recognized applications is for the assessment of viable myocardial tissue. As with perfusion, myocardial metabolic functions can also be quantified by PET imaging.

Physiology of metabolic myocardial imaging:

The heart can oxidatively metabolize a variety of substrates to meet its high energy needs. Under post-prandial conditions, plasma insulin levels rise, peripheral lipolysis is inhibited, and there is increased myocardial glucose metabolism [41]. In the fasting state (low insulin levels, increased lipolysis in peripheral adipose tissue, and high circulating free fatty acids [41]) the myocardium preferentially utilizes fatty acids and lactate as aerobic substrates to provide the energy (ATP) necessary for contractile function (unlike other cells in which glucose is the most important substrate). In plasma, fatty acids are transported bound to albumin and enter the myocardial cell either by passive or active transport. Once in the cell, fatty acids undergo oxidative metabolism. Although fatty acids are the preferred myocardial energy substrate, even in the fasting state glucose utilization is variable and can still account for 30-40% of the energy derived from oxidative metabolism [15]. Addtionally, there is an age-related decrease in fatty acid metabolism and a relative increase in glucose metabolism in healthy older individuals [41]. 

Fatty acid beta-oxidation occurs in the mitochondria and is very sensitive to oxygen deprivation. When blood flow is significantly reduced, tissue delivery of oxygen and removal of waste products are also reduced. As a result, oxygen dependent substrate catabolism decreases. Since fatty acids are catabolized by beta oxidation, fatty acid consumption ceases with anoxia (i.e.: a depression of fatty-acid extraction and oxidation will occur in zones of myocardial ischemia or infarction). This decrease in fatty acid utilization is followed by an increased glycolytic flux with glycogen depletion and increased exogenous glucose utilization.

During periods of ischemia or hypoxia the myocyte compensates for the loss of oxidative potential by shifting toward glucose utilization to generate high-energy phosphates [41]. Unfortunately, the amount of energy produced via glycolysis may not be sufficient to sustain mechanical work, but it can be adequate to maintain cell viability--this condition is referred to as hibernating myocardium. Glycolysis can only be maintained if lactate and hydrogen ions (the byproducts of glycolysis) do not accumulate intracellularly. Therefore, blood flow must be sufficient to deliver glucose to the cell and remove the metabolites of the glycolytic pathway. Once perfusion is decreased below a critical level, the tissue concentrations of lactate and hydrogen ions will increase and inhibit glycolysis [14]. This results in a loss of ion concentration gradients across the cell membrane, followed by cell membrane disruption, and cell death [14].

PET Metabolic Myocardial Imaging using ¹⁸F-2-Deoxyglucose (18-FDG) and exam technique:

 ¹⁸F-2-deoxyglucose is one of the agents used for cardiac metabolic imaging. Fluorine-18 has an effective half life of 110 minutes. It is produced by bombarding ¹⁸O with protons and displacing a neutron [¹⁸O (p,n) ¹⁸F]. Chemically ¹⁸F is comparable in size to hydrogen. ¹⁸F has the best resolution of all positron emitters--approaching 2 mm. This is because most of the emitted positrons traveling only about 1.2 mm prior to undergoing an annihilation reaction. For a 10 mCi ¹⁸FDG injection, the effective patient dose is about 7 mSv [43,45].

The agent ¹⁸FDG competes with glucose for facilitated transport into myocardial cells and once inside the cell it competes for phosphorylation by hexokinase. Unlike glucose, however, the phosphorylated form is not further metabolized. Therefore, regional myocardial uptake of ¹⁸FDG reflects regional rates of exogenous glucose utilization. Only about 1 to 4% of the injected dose is trapped in the myocardium, but the target to background ratios are favorable (Heart:Lung [20:1], Heart:Blood [14:1]).

¹⁸FDG uptake in the myocardium is highly dependent on the patient's dietary state [14]. Myocardial glucose utilization is increased by glucose administration (ie: such as following a meal) which stimulates insulin secretion. The increased insulin levels stimulate glucose metabolism, and tissue lipolysis is inhibited [15]. Therefore, in normal myocardium, ¹⁸FDG, uptake will be promoted in association with high glucose/insulin levels, but decreased in the face of high free-fatty acid levels (ie: with fasting). Unlike normal myocardium, regions of severely decreased perfusion (hibernating myocardium) preferentially utilize glucose as an energy substrate during periods of fasting in order to maintain cell viability. It is this difference in substrate utilization between normal and hibernating myocardium that forms the basis for PET myocardial viability imaging.

For metabolic imaging, patients fast for at least 6 hours and then receive a glucose load [27]. Several protocols are available to promote cardiac FDG uptake:

1. Oral glucose loading
2. Hyperinsulinemic euglycemic clamping
3. Administration of nicotinic acid derivatives

In patients with diabetes the increase in plasma insulin levels following glucose loading may be attenuated and the cells may be less able to respond to insulin stimulation [15,27]. Consequently, tissue lipolysis is not inhibited, plasma fatty acid levels remain high, and myocardial glucose uptake can be poor [15]. This can result in suboptimal quality exams. An improvement in image quality can be obtained by waiting 2-3 hours after tracer injection before imaging (at the expense of increased FDG decay) [27]. In diabetic patients following glucose loading, an IV bolus of regular insulin is given according to a sliding scale and the plasma glucose is checked every 15 minutes in order to maintain a stable serum glucose level of approximately 140 mg/dL.

FDG imaging in patients with non-insulin dependent diabetes is also problematic [20]. An oral glucose load and insulin boluses can be used to control blood glucose levels [20]. For a fasting plasma glucose level less than 7 mmol/L, a 25 g oral glucose solution is given; for 7-11 mmol/L , 5 IU of insulin is given I.V.; for a fasting glucose greater than 11 mmol/L, 10 IU of insulin is given I.V. [20]. The plasma glucose level is then measured in 15 minutes and insulin given according to a sliding scale: For 8 mmol/L no insulin is given; for 8-11 mmol/L, 5 IU of insulin is given I.V., and for a glucose level greater than 11 mmol/L, 10 IU of insulin is given I.V. [20].

Hyperinsulinemic-euglycemic clamping: Hyperinsulinemic-euglycemic clamping requires the simultaneous infusion of glucose and insulin to achieve perfect metabolic regulation [22]. With the use of the clamp, high insulin levels, stable glucose levels, and low free fatty acid levels can be obtained [22]. The hyperinsulinemic-euglycemic clamp method has been shown to produce images with the highest myocardial to background ratio [20] even in diabetic patients, however, the method is time consuming and not practical for clinical work [15]. The procedure requires IV's placed in both the left and right arms- one is used for insulin infusion and the other for glucose. Insulin is infused at a rate of 100mU/kg/hr to achieve hyperinsulinemia [22]. A simultaneous glucose infusion (500mL of 20% glucose with 20mL of 14.9% potassium chloride to prevent hypokalemia) is infused at a rate ot 6 mg/kg/min and the rate is adjusted every 10 minutes to maintain normoglycemia [22]. After 60 minutes of clamping, the FDG is administered intravenously [22].

Nicotinic acid derivatives: Nicotinic acid derivatives have also been studied for use with PET FDG myocardial imaging [22]. The agent acipimox inhibits peripheral lipolysis and thereby reduces circulating free fatty acids [22]. Acipimox 250 mg is orally given 2 hours prior to FDG injection. Some centers will also give patients a carbohydrate and protein-enriched meal [22]. Image quality is generally very good (even in patients with diabetes [25]), with uninterpretable exams in about 5% of patients [22]. The effectiveness of this agent in patients with diabetes requires further study [22].

The typical dose used for the exam is 15 mCi infused over a 60 second interval. Images are usually acquired 45 minutes following administration of the radiotracer [30]. When performing attenuation correction with the use of a transmission scan, ideally the transmission scan should be performed prior to FDG injection. Post-injection transmission scans may suffer from emission contamination and the resultant attenuation corrected images can underestimation FDG activity by about 20% unless an emission spillover adjustment is applied [30].

PET FDG imaging for the detection of viable myocardial tissue:

See also discussion for Viability imaging in the cardiac section

Hibernating myocardium represents severely ischemic, but viable myocardial tissue. In this condition there is a chronic reduction in myocardial metabolism and contractility in order to match a long-standing decrease in blood supply (chronic ischemia). In other words, the cells maintain viability, but energy production is insufficient to maintain mechanical work and contractile dysfunction results [1]. This may be a protective response by the myocytes to reduce their oxygen demand in the setting of reduced oxygen availability. This is a reversible phenomenon and ventricular contractile dysfunction can improve if flow is restored. Because enhanced left ventricular function after revascularization is associated with improved survival, it is crucial to identify areas of viable myocardial tissue.

Evaluation of glucose metabolism using ¹⁸FDG remains the gold standard for the evaluation of myocardial viability (hibernating myocardium) [1,6,19]. Ischemic, but viable myocardium (hibernating) utilizes glucose in preference to other substrates. Ischemic myocardium will therefore concentrate an increased amount of ¹⁸FDG compared to normal myocardium. Increased utilization of glucose can also be seen in myocardium recovering from a recent ischemic event as enhanced anaerobic glycolytic activity persists for some time after reperfusion, despite the availability of adequate oxygen. 

The viability examination is usually performed following some form of glucose loading even though this seems to be contradictory. It would seem most logical to perform ¹⁸FDG myocardial viability imaging in the fasting state when normal myocardial glucose utilization is very low (normal myocardium uses fatty acids for energy substrate in the fasting state). Unfortunately, fasting ¹⁸FDG imaging of the myocardium may be overly sensitive -- detecting small, clinically insignificant areas of myocardial viability because of low background myocardial activity. Additionally, the normal myocardium can be difficult to define in the fasting state and the tracer may not clear adequately from the blood, which can result in image degradation. The one drawback of glucose loading exams is that myocardial substrate utilization will shift from fatty acids to glucose and small areas of viable myocardium may be missed. In either case, the average positive predictive accuracy for detecting viable myocardium by fasting FDG studies is about 85% and is similar to post-glucose loading exams (81%).

Severely decreased FDG uptake below 50% of normal myocardial activity is generally considered indicative of scar, while uptake greater than 50% of normal myocardial activity is indicative of viability. However, determination of ischemic, but viable myocardium can only be made in relationship to a perfusion study [7]. The perfusion exam does not need to be performed with a PET agent; it can be performed using SPECT tracers such as thallium or technetium agents [18]. When regional myocardial ¹⁸FDG uptake is disproportionately enhanced when compared with regional myocardial blood flow, the pattern is termed a perfusion-metabolism mismatch. In the setting of chronic coronary artery disease, a perfusion-metabolic mismatch is highly predictive of myocardial viability and indicates a high likelihood of improved cardiac function following revascularization (improved contractility is seen in 80%-85% of cases and the average improvement in ejection fraction (EF) is 15%).

A scar is characterized by concordant reduction in perfusion and FDG uptake (a FDG-perfusion match) [14]. Improved wall motion is seen in only 8-17% of matched perfusion-metabolic defects [14]. Based on the severity of the perfusion and FDG deficit, the matched pattern may be categorized as a transmural match (absent or markedly reduced perfusion and FDG uptake) or a non-transmural match (mild to moderately reduced perfusion and FDG uptake). When tracer activity equals 50 to 60% or more of peak activity, the matches are mild and probably represent a non-transmural scar [14]. Contractile reserve is more likely to be seen in regions of non-transmural MI [23]. If quantification is performed, viable myocardium is very unlikely to exist if the basal myocardial blood flow is less than 25 ml/min/100 gm [8].

Although the uptake of ¹⁸FDG can discriminate between viable and non-viable tissue, the regional myocardial blood flow and ¹⁸FDG uptake pattern is similar for varying types of myocardial dysfunction. Clinical symptoms are necessary to determine the exact etiology of the scan findings. For instance, increased utilization of glucose can also be seen in myocardium recovering from a recent ischemic event as enhanced anaerobic glycolytic activity persists for some time after reperfusion, despite the availability of adequate oxygen. Different conditions may also coexist in the same myocardial regions.

Prognostic Implications of FDG PET Myocardial Imaging (General):

Cardiac events and mortality:

PET studies have shown that cardiac morbidity and mortality is increased in patients with flow-metabolic mismatches [18,57]. Up to 50% of patients that demonstrate a perfusion-metabolic mismatch will have a cardiac event in the subsequent 12 months in the absence of intervention. The greater the number of mis-matched segments identified, the greater the risk for subsequent cardiac event if revascularization is not performed [18]. The incidence of cardiac events drops to 15% in these patients if revascularization is performed [9]. In two other studies, mortality ranged between 4 to 12% in the group with matched defects, and between 33 and 41% in the mismatch group. In the mismatch group, if revascularization was performed, mortality dropped to between 4 and 12% [7]. In a meta-analysis of patients with viable myocardium, revascularization was found to be associated with an approximately 80% reduction in annual mortality [44].

In patients with underlying left ventricular dysfunction:

It is well recognized that in patients with coronary artery disease (CAD) on medical therapy, the presence of left ventircular (LV) dysfunction is associated with a high mortality. In the Coronary Artery Surgery Study (CASS), mortality of medically treated patients was related to the severity of LV dysfunction with up to 25% annual mortality in patients with resting LVEF's below 25%. In patients with LVEF's below 35% survival was better in those patients undergoing revascularization. Unfortunately, revascularization cannot be recommended in all patients with poor LV function because the surgery is associated with a 5 to 35% mortality in this subgroup. Ideally, the surgery should be performed only in those patients with a high likelihood of improved LV function.

In patients with symptoms of cardiac failure a PET pattern of perfusion-metabolic mismatch identifies a subgroup of patients who are at very high risk for cardiac death on medical therapy (30-40%). These patients are most likely to show significant clinical improvement and have prolonged survival as a result of revascularization [1,18]. Hence, PET can be used to select the appropriate cohort of patients most likely to benefit from surgery and avoid the cost and risks of this procedure if the patient will have no benefit (resulting in an overall cost reduction) [47]. PET results can alter clinical decision making regarding revascularization in approximately 60% of patients [47].

For the prediction of improvement in regional LV function after revascularization, ¹⁸FDG -PET imaging has a pooled sensitivity of 88-93%, a specificity of 58-73%, a positive predictive value of 76%, a negative predictive value of 86%-88% [14, 19, 21,57], and an accuracy of 74%-95% [16]. A matched perfusion-metabolism defect is 75%-100% accurate in predicting that segmental wall motion will not improve [16]. Improved wall motion is seen in only 8%-17% of matched perfusion-metabolic defects [14]. Unfortunately, not all patients with evidence of viable myocardium on PET imaging demonstrate improvement in wall motion following revascularization [24]. Despite a substantial amount of viable myocardium these patients may have non-transmural infarcts with endocardial necrosis (the endocardium contributes almost 75% to total wall thickening at rest) [24] or severe ultrastructure damage which limits contractile reserve [34].

For overall left ventricular function, as a general rule, the larger the extent of the perfusion-metabolic mismatch, the greater will be the anticipated improvement in LVEF following revascularization [34]. If 17% [37] to 25% or more of the LV is viable, a significant improvement in LVEF can be expected following revascularization [14]. Patients with large mismatches (more than 18% of the myocardium [44]) also achieve significantly higher functional status compared to patients with minimal or no PET mismatch [34,44]. On average, LVEF has been shown to improve about 10 percentage points in patients with viable myocardium [57].

The perfusion-metabolism mismatch pattern is also predictive of improvement in heart failure symptoms after revascularization [10]. In patients with heart failure symptoms and a PET perfusion-metabolic mismatch, 70% had improvement in symptoms following revascularization, while only 30% without a mismatch experienced improvement. Improvement in heart failure symptoms correlates with the preoperative extent of viable myocardium [37]. Patients with a PET mismatch pattern involving 18% or more of the LV volume appear to show the greatest clinical benefit [37]. In patients with ischemic cardiomyopathies being considered for revascularization, LVEF and LV volume information determined from gated FDG PET provide incremental prognostic value [35]. Patients with LVEF's below 25% or EDV's greater than 260 mL may not demonstrate improvement in heart failure symptoms following revascularization (although they may still derive a survival benefit) [35]. This is most likely related to advanced ventricular remodeling [35].

In the Immediate Post Infarct Period:

In the immediate post infarction period (out to 1-week post event) the functional outcome of infarcted segments with a flow-metabolism mismatch pattern is more variable and does not necessarily imply recovery of contractile function following revascularization (ie: in the post infarct period PET may overestimate the potential for recovery) [8].

Limitations of PET metabolic imaging:

Limitations of FDG imaging include limited data in diabetic patients and recent reports that suggest that increased FDG accumulation can be seen in acute evolving myocardial infarctions [1, 11]. In the immediate post infarction period (out to 1-week post event) the functional outcome of infarcted segments with a flow-metabolism mismatch pattern is more variable and does not necessarily imply recovery of contractile function following revascularization (for example, in the post infarct period PET may overestimate the potential for recovery) [8]. Also, in the evaluation of FDG-PET for myocardial viability there is wide variability in the literature regarding patient inclusion criteria and examination protocol [14].

Other Approaches to Metabolic Myocardial Imaging

In addition to standard perfusion-metabolic imaging using ¹⁸FDG, other approaches have also been utilized to assess for viability, including determination of oxidative metabolism with ¹¹C palmitate, uptake and retention of ⁸²Rb, 18F fluoroisonidazole imaging, and the water-perfusable tissue index.

PET Metabolic Myocardial Fatty Acid Imaging

Fatty acids are the major source of energy for the myocardium- long chain fatty acids account for 90% of the myocardial energy requirements in the fasting state.. Fatty acid oxidation generates about 6 times the ATP of glycogen oxidation [59]. When glucose or insulin levels are high, such as after a meal, glucose oxidation increases and fatty acid use is suppressed [2]. During ischemia, glucose again plays a major role in oxidative metabolism, whereas oxidation of long chain fatty acids is greatly reduced [2]. Free fatty acids are transported in the blood bound to albumin [59]. Catecholamines increase the blood concentration of fatty acids [16]. Myocardial uptake and retention of fatty acids has been shown to be affected by ischemia [59]. During ischemia, fatty acid metabolism is affected in a matter of seconds [58].

C-11 palmitate

Carbon-11 is a cyclotron produced positron emitter with a half-life of 20.4 minutes and a positron range of 0.4 mm [44]. ¹¹C can be labeled to long-chain fatty acids to study myocardial metabolism [44].

Long-chain free fatty acids easily pass through the sarcolemmic membrane to be activated as acylcoenzyme A (CoA). Acyl CoA is carried into mitochondria through an acyl carnitine carrier system to enter the beta-oxidation pathway. After beta-oxydation , acetyl CoA is formed and enters into the tricarbonic acid cycle for further oxidation to become water and carbon dioxide. Palmitic acid comprises approximately 25 to 30% of the circulating fatty acid in the blood and serves as one of the primary sources for energy production by the heart. The distribution of C-11 labeled palmitic acid reflects efficiency of myocardial energy production.

After initial uptake of the tracer, there is a rapid clearance component which corresponds to levels of beta-oxidation. This is followed by a slower clearance component which reflects incorporation of the tracer into triacylglycerols and phospholipids.

In normal myocardium, there is homogeneous distribution of the tracer. The half-time of washout after extraction is about 12-18 minutes in the normal heart- reflecting the pathway of tracer uptake, beta-oxidation, and efflux of the end product (CO₂) [58]. During periods of ischemia, the uptake of the agent and the rate of the rapid clearance phase and its magnitude markedly diminish, consistent with diminished oxidative metabolism. Delayed clearance is also observed from ischemic and infarcted regions as a result of decreased fatty acid oxidation. C-11 palmitate exams reveal segmental reductions of blood flow in acutely ischemic myocardium are associated with delayed clearance of ¹¹C-palmitate and an increase in 18-FDG uptake.

The rapid blood clearance of this agent and loss of radioactivity from myocardial tissue due to straight-chain fatty-acid catabolism by beta oxidation complicate data analysis. A drawback of this agent is that it is affected by plasma substrate concentrations--in the fasting state, when glucose levels are low, fatty-acid metabolism is accelerated and C-11 palmitate washout is rapid. Washout decreases markedly with glucose loading. The critical organ is the liver.

1-[¹¹C] acetate

Another agent, 1-[¹¹C] acetate can also be used to assess overall oxidative metabolism. The tracer is well extracted by the myocardium and is then converted to acetyl-CoA. Acetyl-CoA is the entry point for all metabolic pathways into the tricarboxylic acid cycle within the mitochondria. Oxidation of acetyl-CoA leads to the production of C-11 labeled CO₂ reflecting the activity of the tricarboxylic acid cycle that, under normal conditions, reflects overall oxidative metabolism (i.e: the efflux of labeled CO₂ after the administration of C-11 acetate reflects myocardial oxygen consumption [58]).

Even in the face of changing patterns of myocardial substrate use, the clearance of 1-[¹¹C] acetate accurately delineated overall oxidative metabolism (ie: unlike C-11 palmitate, this agent is not affected by plasma substrate concentrations). The maintenance of oxidative metabolism in jeopardized myocardium was identified as a prerequisite to recovery of function following revascularization. Myocardial uptake and clearance are homogeneous in normal subjects. In infarcted myocardium, there is decreased uptake and clearance of the tracer due to the reduced oxygen consumption.

The predictive accuracy of this tracer in viability assessment may be superior to FDG. In one study, 15% of nonviable myocardial regions demonstrated increased uptake of FDG relative to flow, but diminished levels of oxidative metabolism, while 20% of viable segments (demonstrating normal oxidative metabolism) had reduced FDG accumulation [11].

Rubidium-82

For Rb-82 imaging in the evaluation of myocardial viability there is unfortunately no association between the severity of a fixed defect on ⁸²Rb imaging and the likelihood of myocardial viability in that area. In defects containing less than 50% relative activity, 30% were shown to be viable by FDG imaging [13].

18F-Fluoromisonidazole

¹⁸F-Fluoromisonidazole has been shown to have increased retention in hypoxic, non-infarcted myocardium. It can therefore be useful for the selective delineation of hypoxic, but viable tissue.

H2¹⁵0 Water

(H2¹⁵O) can be used to determine the water-perfusable tissue index. Contractile function is thought to improve after revascularization only if the perfusible tissue fraction is at least 70%.

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